Device and method for fixating a suture anchor in hard tissue

ABSTRACT

A suture anchor suitable for being fixed in a hard tissue opening with the aid of a material having thermoplastic properties and energy transmitted to the suture anchor for in situ liquefaction of at least part of the material having thermoplastic properties. The suture anchor includes an anchor foot and a thermoplastic sleeve, and the anchor foot includes a system of channels and/or grooves with a mouth in a proximal face of the anchor foot. The thermoplastic sleeve is arranged coaxially to the mouth. The anchor foot also includes a locking element for securing the suture in a non-slideable manner relative to the hard tissue or a securing sleeve for securing the suture. The locking element or the securing element may be secured relative to the anchor foot when the anchor foot is in a fixed state.

FIELD OF THE INVENTION

The invention is in the field of medical technology and concerns adevice and a method for fixating a suture anchor and therewith a suturein hard tissue in particular for attaching, with the aid of the suture,soft tissue to the hard tissue, wherein the hard tissue is in particularbone tissue of a human or animal patient. The invention also concerns ananchor applicable in the method according to the invention.

BACKGROUND OF THE INVENTION

The publication WO 2009/109057 (Woodwelding) discloses devices andmethods for attaching a suture to hard tissue with the aid of a sutureanchor, wherein the suture anchor comprises a material havingthermoplastic properties and is anchored in a hard tissue opening withthe aid of vibratory energy used for in situ liquefaction of thematerial having thermoplastic properties. The liquefied materialpenetrates into pores or other suitable structures of the hard tissue inthe hard tissue opening, where on re-solidification it constitutes apositive fit connection between the hard tissue and the suture anchor.The devices as disclosed in the named publication comprise a vibrationsource in a housing, a vibration tool, a guide tube, the anchor, thesuture and possibly a pushing bush. The proximal end of the vibrationtool is coupled to the vibration source, the proximal end of the guidetube is supported on the housing, the anchor is arranged at the distalend of the vibration tool. The anchor comprises the material havingthermoplastic properties in the form of a thermoplastic sleeve, theanchor or the vibration tool reaching through the sleeve and the sleevebeing clamped between a foot piece of the anchor and the vibration tool,the guide tube or the pushing bush. A suture loop is held in the footpiece of the anchor, two suture end sections extending through furtherparts of the anchor and through portions of the vibrating tool and theguide tube from where they exit to possibly be kept straightened ortensioned by being attached to the guide tube or the housing.

For implantation, an opening is provided in the hard tissue and thedistal end of the device or the suture anchor respectively is introducedinto the opening, such that at least part of the thermoplastic sleeve islocated in the opening, wherein a cross section of the opening isslightly larger than the cross section of the thermoplastic sleeve suchthat the material having thermoplastic properties is located near thehard tissue of the wall of the opening, but such that, on introducingthe anchor into the opening, there is no friction between the sleeve andthe wall of the opening. The vibration source is then activated and thematerial having thermoplastic properties of the thermoplastic sleevebeing clamped between a vibrating element (vibration tool or anchor footbeing coupled to the vibration tool) and a counter element (anchor footnot being coupled to the vibration tool, guide tube or pushing bush) isliquefied starting from its proximal and/or distal face and flows intothe hard tissue, whereby the thermoplastic sleeve gets shorter. Formaintaining the clamping force on the thermoplastic sleeve while thelatter is getting shorter, device elements are moved relative to eachother in an axial direction which is preferably effected by apre-tensioned spring arranged together with at least the thermoplasticsleeve and the elements between which the thermoplastic sleeve isclamped in a closed load frame. This measure allows automatic anchoringof the suture anchor, the surgeon only having to position the devicewith the distal end of the guide tube on the surface of the hard tissueand to activate the vibration source. However, special measures areneeded for allowing checking and tuning of the device before theanchoring process, without liquefaction of the material of thethermoplastic sleeve.

The publication US 2009/131947 (Woodwelding) also discloses a method forattaching a suture to hard tissue with the aid of a suture anchorcomprising a thermoplastic material which is liquefied in situ with theaid of vibratory energy. The disclosed method is based on the sameprinciple as the method which is briefly described above, wherein thesuture is threaded through a distal end portion of the anchor, wherein aproximal end portion of the anchor comprises the thermoplastic material,and wherein a proximal face of the anchor is held against a distal faceof a vibrating tool by pulling suture end portions in a proximaldirection.

Further methods and devices for attaching sutures to hard tissue withthe aid of suture anchors are disclosed in the publications U.S. Pat.No.-7,678,134, U.S. Pat. No.-7,695,495, US-2006/161159, US-2009/192546,US-2009/187216 (all to Arthrex), U.S. Pat. No.-5,733,307 (Dinsdale), orU.S. Pat. No.-6,508,830 (Steiner), wherein the disclosed anchorscomprise an interference screw to be screwed into a bone openingprovided for the purpose or a plug preferably made of bone material andto be press-fitted into a bone opening provided for the purpose, whereinthe suture is either held by the screw or plug or by an additionalelement being retained in the opening with the aid of the screw or plug.

Methods of anchoring an item in an opening provided in hard tissue, e.g.in bone tissue of a human or animal patient with the aid of a materialhaving thermoplastic properties which is liquefied in situ and made topenetrate the hard tissue of the wall of the opening are disclosed inthe publications U.S. Pat. No.-7,335,205, U.S. Pat. No.-7,008,226,US-2006/0105295, US-2008/109080, US-2009/131947, WO-2009/109057, andWO-2009/132472. The disclosure of all these publications andapplications is enclosed herein by reference.

BRIEF SUMMARY OF THE INVENTION

Generally speaking, it is the object of the invention to create afurther device and method for fixating a suture anchor and therewith asuture in hard tissue, wherein the suture fixated in the hard tissuewith the aid of the suture anchor is to be in particular suitable forattaching soft tissue to the hard tissue, wherein the hard tissue is inparticular bone tissue of a human or animal patient, and wherein one ofthe method steps comprises in situ liquefaction of a material havingthermoplastic properties and bringing the liquefied material intocontact with the hard tissue. The suture anchor is fixated in a hardtissue opening by penetration of the liquefied material into hard tissuewalls of the opening or it is fixated beyond a hard tissue opening bythe liquefied material expanding (flowing in radial direction) beyondthe opening, i.e. on a non-accessible side of a hard tissue layer,possibly combined with penetrating the hard tissue surface on thisnon-accessible side of a hard tissue layer. On re-solidification thematerial which penetrated into the hard tissue constitutes a positivefit connection between this hard tissue and the anchor and/or thematerial expanded beyond the hard tissue opening constitutes a bodywhich cannot pass the opening. The improvement achieved by the inventionas compared with state of the art methods and devices serving the samepurpose concern in particular the simplicity of method and device.

In particular, it is an object of the invention to create a furtherdevice and a further method for fixating a suture anchor in or beyond anopening in hard tissue of a human or animal patient, the suture anchorand the fixation being suitable in particular for the suture fixatedwith the aid of the suture anchor to be slideable relative to the anchorbeing fixated in the hard tissue. Therein, fixation of the suture anchorin the hard tissue, in particular underneath a cortical bone layer is tobe effected with the aid of a material having thermoplastic propertiesand being liquefied in situ to be brought into contact with the hardtissue, in particular to penetrate into natural pores (trabecularstructure) of the hard tissue or into suitable structures or cavitiesprovided in the hard tissue, to preferably form, on re-solidification, apositive fit connection between the anchor and the hard tissue. Thedevice and the method according to the invention are to constitute animprovement over the known state of the art, in particular regardingstability and simplicity of the device and simplicity of the wholefixation process including preparatory steps. Device and methodaccording to the invention are to be suitable in particular forminimally invasive surgery but are to be applicable in open surgeryalso.

Device and method according to the invention constitute a furtherdevelopment of the devices and methods as disclosed in WO 2009/109057,the disclosure of which is included herein by reference in its entirety.Therein, the device is improved regarding stability against lateralforces acting on the anchor when arranged on a distal tool end and it issimplified by not needing a guide sleeve. Furthermore, it may comprisemeans for an easy mechanical and possibly visual control of theliquefaction of the material having thermoplastic properties. Inaddition, the device according to the invention may comprise a leversystem which is operated by the surgeon and which facilitates handlingof the suture, i.e. constitutes means for attaching, tensioning andmoving the suture. The device according to the invention is easilyoperated by the surgeon with one hand, wherein he is able to operate thelever system with one finger of this hand. The lever system simplifiesnot only the implantation process but also the steps for preparing thedevice for the implantation process.

The device according to the invention comprises a tool with a proximalend suitable for being coupled to the energy source and a distal endsuitable for arrangement of the suture anchor including the suture. Inaddition, the device comprises a substantially tube-shaped interfacepiece, which serves for stabilizing the anchor at the distal end of thetool, such that it can be safely positioned relative to the hard tissueand is kept aligned with the tool during the fixation procedure. Theinterface piece is designed to be displaceable in an axial channel ofthe distal tool end during the fixation procedure and to be removablefrom the fixation site together with the tool.

The device may further comprise an anchor including a suture, andpossibly the energy source, the anchor being arranged at the distal endof the tool and the energy source being coupled to the proximal end ofthe tool. The energy source or a housing thereof may carry the abovenamed lever system. The anchor comprises the material havingthermoplastic properties in the form of a thermoplastic sleeve which isheld between a distal tool face and an anchor foot and which, in thefixation process, is at least partly liquefied preferably starting fromits proximal face in contact with the distal tool face, whereby theliquefied material flows away in a radial direction to penetrate hardtissue surrounding the liquefaction location or a cavity provided inthis hard tissue, or to expand into soft tissue or a cavity beyond thehard tissue. For keeping the thermoplastic sleeve in close contact withthe distal tool face during the liquefaction process the anchor foot ispulled relative to the tool in proximal direction with the aid of thesuture, which is effected by the surgeon advantageously with the aid ofthe above named lever system.

The interface piece is dimensioned to reach through the thermoplasticsleeve, a distal end of the interface piece being couplable or coupledto the anchor foot and a proximal end reaching into an axial channel ofthe tool. During the liquefaction process the thermoplastic sleeve getsshorter and the anchor foot together with the interface piece are movedrelative to the tool in a proximal direction. For mechanical control ofthe liquefaction process the tool may comprise a stop against which theproximal face of the interface piece abuts when the thermoplastic sleevehas reached a desired minimal axial length. For an additional visualcontrol the tool may comprise a lateral recess or a see-through portionadjoining the stop distally, in which recess or see-through portion themovement of the proximal end of the interface piece can be visuallycontrolled, during minimally invasive surgery through an arthroscope orduring open surgery directly by the surgeon. For being removabletogether with the tool from the fixation site after completion of thefixation, the interface piece is caught in the axial channel of the toolat the latest on completion of the fixation process, such that it cannotbe removed from the channel in a distal direction. The anchor foot ispreferably connected with the interface piece with the aid of a push-onor clip-on connection which holds the two elements together when underno load, which stabilizes the two elements relative to each other undera compressive load, and which is de-connected easily under a smalltensile load.

The suture runs in a loop through a system of channels and/or grooves inthe anchor foot, the two end sections of the suture protruding from theproximal face thereof and running from there through the interface pieceand the axial channel of the tool from where they exit preferablythrough the above named recess. The system of channels and/or grooves ispreferably dimensioned such that the suture is easily slideabletherethrough and such that, during implantation, the suture comes intocontact neither with the hard tissue in the tissue opening nor with theliquefied material. This measure achieves that neither friction on thehard tissue nor thermal or mechanical influence of the liquefied orre-solidified material of the thermoplastic sleeve will impair theslideability of the suture through the implanted anchor. This does notonly mean that after anchorage of the suture anchor the suture is heldslideably by the latter but it also means that the suture may well be ofa friction and/or heat sensitive type, consisting e.g. of a materialhaving similar characteristics as the material of the thermoplasticsleeve.

For the fixation process, the tool is preferably supported on the hardtissue. For achieving liquefaction underneath a cortical bone layer oron a non-accessible side of a bone plate, the tool comprises a step at adistance from the distal tool face adapted to the thickness of thecortical bone layer or the bone plate. Therein the tool portion on thedistal side of the step has a cross section smaller than the crosssection of the opening and a tool portion on the proximal side of thestep has a cross section larger than the cross section of the opening,such that the step limits introduction of the distal device end into thehard tissue opening by abutting against the hard tissue surface, whenthe interface between the distal tool face and the proximal face of thethermoplastic sleeve and therewith the liquefaction location is situatedjust below the cortical bone layer or on the other (non-accessible) sideof the bone plate. During the liquefaction process, the tool is kept inthe same position.

The energy source is preferably a vibration source, in particular asource of ultrasonic vibration (e.g. piezoelectric vibration generatorpossibly comprising a booster to which the tool is coupled) and the toolis suitable for transmission of the vibration from its proximal end toits distal face, preferably such that the distal face vibrates with amaximal longitudinal amplitude. For the in situ liquefaction theproximal face of the thermoplastic sleeve is held against the vibratingdistal tool face, such creating friction heat at the interface. It ispossible also to activate the tool to vibrate in a radial or in arotational direction.

Alternatively, the energy source may be a laser, preferably emittinglaser light in the visible or infrared frequency range and the tool isequipped for transmitting this light to its distal end, preferably viaglass fiber. For the in situ liquefaction the laser light is absorbednear the distal tool face or in the thermoplastic sleeve held againstthe distal tool face, wherein in the latter case the material of thethermoplastic sleeve may contain particles or substances effecting suchabsorption. Furthermore, the energy source may be a source of electricenergy which e.g. heats an electric resistor in a distal tool portion orwhich causes eddy currents and therewith thermal energy near the distaltool face or in the thermoplastic sleeve.

Suitable in situ liquefaction of a material having thermoplasticproperties with the aid of vibration energy combined with an acceptablethermal loading of the tissue and suitable mechanical properties of thepositive fit connection to be produced is achievable by using materialswith thermoplastic properties having an initial modulus of elasticity ofat least 0.5 GPa and a melting temperature of up to about 350° C. incombination with vibration frequencies preferably in the range ofbetween 2 and 200 kHz (preferably 15 to 40 kHz, or even more preferablybetween 20 and 30 kHz). The modulus of elasticity of at least 0.5 GPa isin particular necessary if the material having thermoplastic propertiesis to transmit the vibration or mechanical forces without loss ofmechanical stiffness. If the material having thermoplastic properties isnot to transmit the vibration but is to be liquefied where it is indirect contact with the vibrating tool or if the material havingthermoplastic properties is to transmit the vibration or mechanicalforces, but is supported and guided by device parts of other materials,the material having thermoplastic properties may have a considerablysmaller modulus of elasticity.

Materials having thermoplastic properties suitable for the thermoplasticsleeve of the device and the method according to the invention arethermoplastic polymers, e.g.: resorbable or degradable polymers such aspolymers based on lactic and/or glycolic acid (PLA, PLLA, PGA, PLGAetc.) or polyhydroxy alkanoates (PHA), polycaprolactone (PCL),polysaccharides, polydioxanes (PD) polyanhydrides, polypeptides orcorresponding copolymers or composite materials containing the namedpolymers as a component; or non-resorbable or non-degradable polymerssuch as polyolefines (e.g. polyethylene), polyacrylates,polymetacrylates, polycarbonates, polyamides, polyester, polyurethanes,polysulfones, polyarylketones, polyimides, polyphenylsulfides or liquidcrystal polymers LCPs, polyacetales, halogenated polymers, in particularhalogenated polyolefines, polyphenylensulfides, polysulfones, polyethersor equivalent copolymers or composite materials containing the namedpolymers as a component.

Specific embodiments of degradable materials are Polylactides like LR706PLDLLA 70/30, R208 PLDLA 50/50, L210S, and PLLA 100% L, all ofBöhringer. A list of suitable degradable polymer materials can also befound in: Erich Wintermantel und Suk-Woo Haa, “Medizinaltechnik mitbiokompatiblen Materialien und Verfahren”, 3. Auflage, Springer, Berlin2002 (in the following referred to as “Wintermantel”), page 200; forinformation on PGA and PLA see pages 202 ff., on PCL see page 207, onPHB/PHV copolymers page 206; on polydioxanone PDS page 209. Discussionof a further bioresorbable material can for example be found in CABailey et al., J Hand Surg [Br] 2006 Apr.; 31(2): 208-12.

Specific embodiments of non-degradable materials are Polyetherketone(PEEK Optima, Grades 450 and 150, Invibio Ltd), Polyetherimide,Polyamide 12, Polyamide 11, Polyamide 6, Polyamide 66, Polycarbonate,Polymethylmethacrylate, Polyoxymethylene, or polycarbonate-urethane(e.g. Bionate by DSM, in particular types 65D and 75D). An overviewtable of polymers and applications is listed in Wintermantel, page 150;specific examples can be found in Wintermantel page 161 ff. (PE,Hostalen Gur 812, Höchst AG), pages 164 ff. (PET) 169 ff. (PA, namely PA6 and PA 66), 171 ff. (PTFE), 173 ff. (PMMA), 180 (PUR, see table), 186ff. (PEEK), 189 ff. (PSU), 191 ff (POM—Polyacetal, tradenames Delrin,Tenac, has also been used in endoprostheses by Protec).

The material having thermoplastic properties may further contain foreignphases or compounds serving further functions. In particular, thethermoplastic material may be strengthened by admixed fibers or whiskers(e.g. of calcium phosphate ceramics or glasses) and such represent acomposite material. The material having thermoplastic properties mayfurther contain components which expand or dissolve (create pores) insitu (e.g. polyesters, polysaccharides, hydrogels, sodium phosphates),compounds which render the implant opaque and therewith visible forX-ray, or compounds to be released in situ and having a therapeuticeffect, e.g. promotion of healing and regeneration (e.g. growth factors,antibiotics, inflammation inhibitors or buffers such as sodium phosphateor calcium carbonate against adverse effects of acidic decomposition).If the thermoplastic material is resorbable, release of such compoundsis delayed. If the device is to be anchored, not with the aid ofvibration energy, but with the aid of electromagnetic radiation, theliquefiable material having thermoplastic properties may locally containcompounds (particlulate or molecular) which are capable of absorbingsuch radiation of a specific frequency range (in particular of thevisible or infrared frequency range), e.g. calcium phosphates, calciumcarbonates, sodium phosphates, titanium oxide, mica, saturated fattyacids, polysaccharides, glucose or mixtures thereof.

Fillers used may include degradable, osseostimulative fillers to be usedin degradable polymers, including: β-Tricalciumphosphate (TCP),Hydroxyapatite (HA,<90% crystallinity); or mixtures of TCP, HA, DHCP,Bioglasses (see Wintermantel). Osseo-integration stimulating fillersthat are only partially or hardly degradable, for non degradablepolymers include: Bioglasses, Hydroxyapatite (>90% cristallinity),HAPEX®, see SM Rea et al., J Mater Sci Mater Med. 2004 Sept.; 15 (9):997-1005; for hydroxyapatite see also L. Fang et al., Biomaterials 2006Jul.; 27 (20): 3701-7, M. Huang et al., J Mater Sci Mater Med 2003 Jul.;14 (7): 655-60, and W. Bonfield and E. Tanner, Materials World 1997 Jan;5 no. 1:18-20. Embodiments of bioactive fillers and their discussion canfor example be found in X. Huang and X. Miao, J Biomater App. 2007 Apr;21 (4): 351-74), JA Juhasz et al. Biomaterials, 2004 Mar.; 25 (6):949-55. Particulate filler types include: coarse type: 5-20 μm(contents, preferentially 10-25% by volume), sub-micron (nanofillers asfrom precipitation, preferentially plate like aspect ratio>10, 10-50 nm,contents 0.5 to 5% by volume). Experiments show that liquefaction withthe aid of ultrasonic vibration energy allows filling the thermoplasticpolymer to a relatively high degree without impairing the capability ofthe liquefied material to penetrate structures as e.g. the trabecularstructure of viable cancellous bone.

Anchor portions other than the thermoplastic sleeve may consist of anysuitable material (e.g. polymer, metal, ceramic, glass) which materialmay be bio-resorbable or not bio-resorbable and liquefiable or notliquefiable. Non-bioresorbable or non-biodegradable such materials maycomprise surfaces equipped for furthering osseointegration (e.g. per seknown surface structures or coatings) where in contact with the bonetissue, in particular if the material of the thermoplastic sleeve isbio-resorbable or bio-degradable and therefore the anchoring functionneeds to be gradually taken over by osseointegration. Good results havee.g. been achieved with anchor feet of polylactic acid (P LA) filledwith Hydroxyapatite or calciumphosphates, in particular of PLLA filledwith 60% tricalciumphosphate or PDLLA 70%/30% (70%L and 30%D/L) filledwith 30% biphasic calciumphosphate, combined with thermoplastic sleevesof PLDLLA 70%/30% (70%L and 30% D/L), as available from BOhringer asLR706. The PDLLA 70%/30% filled with 30% of biphasic calcium phosphateand similar materials prove to be suitable also for the thermoplasticsleeve and therefore suitable for manufacturing bio-resorbable,one-piece anchors being made of one material only.

As the tool can be designed very slim and with an axial length of 200 mmor even longer, the device and method according to the invention are inparticular suitable for minimally invasive surgery but are alsoapplicable in open surgery. If the tool is a vibration tool, itpreferably has a length corresponding to half of the vibrationwavelength in the tool material (or a multiple thereof). This half ofthe vibration wavelength is e.g. in titanium grade 5 and at a vibrationfrequency of 20 kHz 126.5 mm.

Device and method according to the invention as far as above describedare applicable for all surgical procedures in a human or animal patient,in which surgical procedure a suture needs to be attached to hardtissue, in particular attached to be at least primarily slideablerelative to the implanted anchor, and in particular to bone tissue witha cortical bone layer wherein the fixation of the anchor is preferablyachieved underneath the cortical bone layer (so called sub-corticalfixation) in cancellous bone situated underneath the cortical bonelayer, on the inner side of the cortical bone layer, or in a cavity orsoft tissue adjoining the cortical bone layer on its inner side. In thesame manner, the device and the method according to the invention areapplicable for attaching a suture to a replacement material havingfeatures comparable to the features of hard tissue, or to part hardtissue part replacement material, or to a further implant (e.g.endoprosthesis) wherein the implant needs to be suitably equipped, e.g.with undercut openings. An example of such an application is thefixation of a soft tissue end to a bone, e.g. fixation of a rotator cuffto underlying bone tissue (or a corresponding endoprosthesis), Achillestendon repair, or fixation of another ligament or tendon end to bonetissue using the technique of the so called double row procedure. Forthis procedure sutures are slideably attached to the bone by a row ofmedial anchors, are passed through the soft tissue, tensioned and,crossing each other, are non-slideably fixed (locked) with the aid of arow of lateral anchors, this second row running substantially parallelto the row of medial anchors.

When using the above discussed device and method according to theinvention for the slideable attachment of the sutures, i.e. foranchoring the medial anchors, with the aid of the material havingthermoplastic properties and preferably vibration energy it isadvantageous to use a similar technique for the non-slideable attachmentor locking of the sutures, i.e. for anchoring the lateral anchors, also.

As described further below, it is possible also to use the device andthe method according to the invention not only for slideable fixation ofa suture relative to a hard tissue but also for non-slideable suchfixation or locking of the suture relative to the hard tissuerespectively.

BRIEF DESCRIPTION OF THE DRAWINGS

Device and method according to the invention are described in furtherdetail in connection with the appended Figs., wherein:

FIG. 1 illustrates an exemplary embodiment of the device according tothe invention by showing a distal portion of the device before theanchoring procedure and after the anchoring procedure, this distaldevice portion comprising a distal portion of the tool, the interfacepiece, the suture anchor and the suture running through the anchor;

FIG. 2 shows the suture anchor as shown in FIG. 1 being fixated in thehard tissue opening;

FIG. 3 shows a further exemplary embodiment of the distal tool portionand the interface piece of a device according to the invention;

FIGS. 4 and 5 further illustrate an exemplary embodiment of the deviceaccording to the invention by showing an exemplary embodiment of theproximal portion of the device comprising a proximal portion of thetool, the energy source with the housing and, attached to the housing,the lever system for fastening and tensioning the suture and for movingthe anchor foot with the aid of the suture;

FIG. 6 illustrates a further exemplary embodiment of the methodaccording to the invention and of the anchor being fixated with the aidof the method;

FIG. 7 illustrates four successive phases of the per se known double rowprocedure using the example of a rotator cuff repair;

FIG. 8 shows the fixated anchor as shown in FIG. 2 and further equippedwith a locking plug for locking the suture relative to the anchor;

FIG. 9 illustrates a further exemplary embodiment of the methodaccording to the invention wherein the suture is locked relative to theanchor with the aid of a locking plug;

FIG. 10 shows the fixated anchor as shown in FIG. 2 and further equippedwith a securing sleeve preventing damage of the edge of the mouth of thehard tissue opening by the suture or of the suture by this edge;

FIG. 11 shows a preferred embodiment of a suture anchor applicable inthe device and method according to the invention;

FIGS. 12 to 15 show the proximal end portion of a vibration tool whichis e.g. applicable in the device and method according to the invention.

DETAILED DESCRIPTION OF THE INVENTION

FIG. 1 shows a distal portion of an exemplary embodiment of the deviceaccording to the invention and illustrates in section the distal end ofa tool 1, the suture anchor 2 and the interface piece 3. Alsoillustrated is the suture 4 (shown as dash-dotted line), which runs in aloop through the anchor 2, suture end sections extending through theinterface piece 3 and through parts of the tool 1. The distal deviceportion is shown positioned relative to the hard tissue opening 5 beforethe liquefaction and anchoring process (left hand side of FIG. 1) andafter this process (right hand side of FIG. 1), wherein the hard tissueopening 5 is e.g. an opening in bone tissue and reaches from a bonesurface 6 through a cortical bone layer 7 into cancellous bone tissue 8.

The tool 1 comprises at its distal end a distal tool face 10 andextending axially from the distal tool face, an axial channel 11. Theaxial channel 11 comprises a first catch element 12, e.g. a wedge-shapedprotrusion and in proximal direction following the first catch element12 a stop 13 which ends the axial channel 11 or closes it at leastpartially. The stop 13 is constituted in the illustrated case by theproximal wall of a lateral recess 14, the recess opening the axialchannel 11 laterally for visual inspection. The tool portion adjoiningthe lateral recess 14 in the proximal direction comprises a groove 15aligned with the lateral recess 14 for accommodation of the suture 4.The tool 1 preferably further comprises an outer step 16, separating adistal end portion 17 of the tool 1 having a smaller cross section froma proximally adjoining portion having a larger cross section. Asillustrated in FIG. 1, it is sufficient for the step 16 to extend onlyaround part of the tool circumference. However it may also run aroundthe whole tool circumference.

The suture anchor 2 comprises the anchor foot 22 and the thermoplasticsleeve 23, wherein the anchor foot 22 and the thermoplastic sleeve 23may be separate items or wherein anchor foot 22 and thermoplastic sleeve23 may constitute one piece. The anchor foot 22 comprises a system ofchannels and/or grooves 25 through which the suture 4 runs in apreferably slideable loop entering and exiting through the proximal faceof the anchor foot 22. As illustrated in FIG. 1, the system of channelsand/or grooves comprises e.g. a transversal first channel 30 extendingsubstantially perpendicular to the anchor foot axis, and in the regionof both mouths of this first channel 30 recesses 31 or grooves, as wellas an axial second channel 32 extending to the proximal face of theanchor foot 22 and being connected to the recesses 31 or grooves throughangled third channels 33.

For accommodation of more than one suture 4 the system of channelsand/or grooves 25 may comprise more than one transversal first channels30 being arranged axially spaced from each other and either parallel toeach other or angled.

The interface piece 3 is substantially tube shaped and designed toextend loosely through the thermoplastic sleeve 23. The interface pieceis coupled (or couplable) at a distal end to the anchor foot 22 andreaches beyond the proximal sleeve face when the distal sleeve face sitson the proximal face of the anchor foot 22. Coupling of the anchor foot22 and the interface piece 3 is effected e.g. as illustrated between atube-shaped anchor foot protrusion into which a distal end portion ofthe interface piece 3 is e.g. press-fitted. Instead of such press-fitcoupling any per se known clip-on connection is applicable for whiche.g. the distal end of the interface piece 3 comprises a ring-shapedridge and the tube-shaped anchor foot protrusion comprises a ring-shapedgroove adapted to the ridge. At its proximal end, the interface piece 3comprises a second catch element 12′, e.g. a depression, adapted to thefirst catch element 12 in the axial channel 11 of the tool 1 andcooperating with this first catch element 12 in a manner as describedfurther below.

The suture anchor 2 is arranged at the distal end of the tool 1 with theproximal end of the interface piece 3 extending into the axial channel11 of the tool 1 and the suture 4 extending from the proximal face ofthe anchor foot 22 through the interface piece 3 into the recess 14 ofthe tool 1 and from there into the groove 15. The thermoplastic sleeve23 is kept between the distal face 10 of the tool 1 and the anchor foot22 by the end sections or the suture 4 being held at a proximal end ofthe tool (see e.g. FIG. 4). The axial lengths of the interface piece 3,the thermoplastic sleeve 23 and the tool section adjoining the recess 14in a distal direction are adapted to each other such that the proximalface of the interface piece 3 is just about visible in the recess 14,when the thermoplastic sleeve 23 has an initial maximum length. The stop13 is distanced from the named position of the proximal face of theinterface piece 3 by the length of the thermoplastic sleeve 23 which isto be liquefied. The catch elements 12 and 12′ are arranged such thatthey catch each other before the proximal face of the interface piece 3abuts the stop 13, the cooperating catch elements limiting distalmovement of the interface piece 3 relative to the tool such that theinterface piece cannot be removed from the channel 11, but possiblyallowing further proximal movement.

In the case of the use of vibrational energy for the liquefactionprocess, it is advantageous to equip the distal face 10 of the tool 1(or the proximal face of the thermoplastic sleeve 23) with energydirectors, e.g. with an edge which limits contact with the thermoplasticsleeve to a line, and/or to rigidly attach the distal face of thethermoplastic sleeve 23 to the anchor foot 22, which is easily possibleif the anchor foot 22 is made of a thermoplastic material, e.g. of PEEKto which the thermoplastic sleeve 23 can be welded. It is also possibleto produce the anchor foot and thermoplastic sleeve as one piececonsisting of the material having thermoplastic properties only (seealso FIG. 11), e.g. of a polylactide polymer, e.g. PDLLA, preferablyPDLLA 70%/30% filled with up to 30% of biphasic calciumphosphate. Allthe named measures help to ensure limitation of the liquefaction of thethermoplastic sleeve 23 to its proximal face. In an anchor foot made ofa polymer prone to creep, it may be advantageous to strengthen the areamost loaded by the suture tension, e.g. by lining the transverse suturechannel 30 with a tube of a more resistant material such as e.g. apolylactide of a higher crystallinity or PEEK or by positioning aportion of such a material proximal to the transverse suture channel 30.

As it is most convenient to provide the hard tissue opening 5 foranchoring the suture anchor 2 by drilling, the anchor and at least thedistal end portion 16 of the tool which is to be positioned in theopening 5 have advantageously a circular cross section. The same appliesto the anchor foot 22, the interface piece 3 and the axial channeltherethrough, as well as to the thermoplastic sleeve 23 and the axialchannel 11 of the tool 1. However, this is not a condition for theinvention, according to which any one of the named items may have anon-circular cross section. The only condition regarding cross sectionsis the condition for the thermoplastic sleeve 23 which is to fit intothe opening 5 such that a sufficient part of the material to beliquefied is situated close to the wall of the opening 5. The crosssection of the distal end portion 17 of the tool 1 and the cross sectionof the anchor foot 22 are preferably the same as the cross section ofthe thermoplastic sleeve 23 or they are slightly smaller than thelatter.

For fixating the suture anchor 2 in the hard tissue opening 5 andtherewith attaching the suture 4 relative to the hard tissue surface 6,the device according to the invention is positioned relative to the boneopening 5 as illustrated on the left hand side of FIG. 1. The energysource is coupled to the proximal end of the tool 1 (not shown), theinterface piece 3 and the anchor 2 are arranged at the distal tool endwith the suture 4 extending through the anchor foot 22, the interfacepiece 3, the axial channel 11 of the tool 1 and the recess 14 and isheld further proximally to be at least straightened or slightlytensioned, such that the thermoplastic sleeve 23 is held between theproximal face 10 of the tool 1 and the anchor foot 22, and the tool 1 ispositioned such that step 16 abuts against the bone surface 6. Forstarting liquefaction of the thermoplastic sleeve 23, the energy sourceis activated and possibly the suture tension increased. The liquefiedmaterial flows radially away from anchor 2 and tool 1 and thethermoplastic sleeve 23 gets shorter and is kept in contact with thedistal face 10 of the tool 1 by pulling the suture 4 in a proximaldirection and therewith pulling the anchor foot 22 nearer to the distaltool face 10, while the step 16 remains in contact with the bone surface6.

The principle of the anchoring process is described (for differentapplications) e.g. in the publication US-2009/131947.

When working with a vibration tool and with a friction and/or heatsensitive suture it is particularly important not to tension the sutureon activation of the energy source, but only when the proximal face ofthe thermoplastic sleeve is at least warmed such that it cannot transmitthe vibration further distally or at least not fully. If the suture istensioned at the moment of starting the vibration, it may happen thatthe vibrations are transmitted through the thermoplastic sleeve into theanchor foot which then vibrates relative to the suture. This may damagea sensitive suture before liquefaction of the thermoplastic sleevestarts. Further measures for preventing vibration transmission to theanchor foot are energy directors at the interface between the tool 1 andthe thermoplastic sleeve as described further above and/or start of thevibration with a smaller starting amplitude which is increased after astarting interval in which the proximal end of the thermoplastic sleeveis warmed up.

With the liquefaction process advancing and the thermoplastic sleeve 23getting shorter and the anchor foot 22 being pulled in a proximaldirection, the interface piece 3 advances in the axial channel 11 of therecess 14 respectively, until the catch elements 12 and 12′ come intocatching interaction with each other and the proximal face of theinterface piece abuts against the stop 13, which signifies the end ofthe liquefaction process as shown on the right hand side of FIG. 1. Theadvancement of the proximal end of the interface piece 3 and therewiththe liquefaction process can be visually controlled in the recess 14.

At the end of the liquefaction process, the thermoplastic sleeve 23 hasa minimal axial length and the liquefied and re-solidified material 40of the thermoplastic sleeve 23 extends radially into the cancellous bone8 and/or anchors the suture anchor 2 securely on the inside of thecortical bone layer 7. Furthermore, the interface piece 3 is caught inthe axial channel 11 of the tool 1, which means on removing the tool 1from the anchored suture anchor, the interface piece 3 is removedtogether with the tool 1.

For making sure that the suture 4 is not clamped between the proximalend of the interface piece 3 and the stop 13, when the proximal face ofthe interface piece abuts the stop 13, it is advantageous to design thisproximal face and/or the stop 13 sloping, such that abutment of theinterface piece 3 on the stop occurs only at the bottom of the recess14, while the suture 4 is pulled away from this bottom, i.e. towards theopening of the recess 14. The named form of the proximal face of theinterface piece 3 also results in an easier resiliency of the abuttingportion of the proximal face of the interface piece 3 which can be madeuse of for the design of the second catch element 12′.

After completion of the liquefaction process, the suture 4 is releasedfrom being tensioned and held, and the tool 1 together with theinterface piece 3 is removed from the opening 5 in which the sutureanchor 2 is now safely anchored, and the suture is slideably attached tothe bone tissue.

FIG. 2 shows the result of the method as illustrated in FIG. 1, i.e. thesuture 4 being attached to the hard tissue with the aid of the sutureanchor 2 being anchored in the hard tissue opening 5 by there-solidified material 40 situated in the hard tissue or bone tissuesurrounding the opening, in particular in the cancellous bone tissue 8just underneath the cortical bone layer 7 (subcortical fixation), there-solidified material 40 being connected to remains of thethermoplastic sleeve 23. Obviously, the fixation process according tothe invention is not dependent on the quality of the cancellous bone 8,which may even be completely absent. In the latter case the liquefiedmaterial may or may not penetrate the inner surface of the cortical bonelayer and be held in the hard tissue opening mainly by the fact ofconstituting after re-solidification a body which cannot pass throughthe opening any more. This means that the fixation according to theinvention is suitable not only for a subcortical fixation in cancellousbone of a reduced mechanical stability but also in absence of cancellousbone e.g. in the medullary cavity of long bones or on a non-accessibleside of a bone plate.

FIG. 3 shows an alternative embodiment of the catch mechanism and thestop mechanism between the tool 1 and the interface piece 3 of a deviceaccording to the invention. The tool again comprises an axial channel 11which extends at least through a distal tool portion and in which thesubstantially tubular interface piece 3 extends, and it comprises arecess 14 in which the proximal end of the interface piece 3 moves in aproximal direction during the liquefaction process. The first catchelement 12 is constituted by the tool face at the distal side of therecess 14, the second catch element 12′ is arranged on a proximalprotrusion of the interface piece 3. The two catch elements keep theinterface piece 3 caught in the axial channel 11 of the tool 1 even whenthe thermoplastic sleeve still has its original (maximum) length. Thismeans that the interface piece which is removed from the tool forattaching the thermoplastic sleeve and the anchor foot to it, is caughtin the axial tool channel 11 already on introducing the proximal end ofthe interface piece into the axial channel for preparing the device forthe fixation procedure. During liquefaction of the material of thethermoplastic sleeve, the second catch element 12′ is distanced in aproximal direction from the first catch element 12 and on removing tool1 and interface piece 3 from the fixation site, the interface piece 3 isdisplaced into its most distal position, in which the two catch elementsare in contact with each other.

The stop 13 of the tool according to FIG. 3 is arranged as step in therecess 14 and interacts with a portion of the proximal face of theinterface piece 3 which portion is approximately opposite to theprotrusion with the second catch element 12′. It is quite possible tonot provide a stop 13 for the interface piece 3. In such a case,proximal movement of the interface piece 3 and the anchor foot will beended at the last, when the thermoplastic sleeve 23 is fully liquefiedand the anchor foot abuts against the distal tool face. It is furtherpossible to limit the liquefaction process via the suture tension whichcan be effected e.g. with the aid of the lever system to be discussed inconnection with FIG. 4.

Method and device according to the invention are suitable e.g. forestablishing the medial anchors in the per se known double row procedurewhich is described further below in connection with FIG. 7 and which isused e.g. for rotator cuff repairs or Achilles tendon repairs. For thisapplication, the suture is to be kept slideable relative to the anchor.Other exemplary applications of method and device according to theinvention are e.g. regarding the human shoulder joint: the Bankartrepair or the repair of SLAP-lesions (superior labrum anterior toposterior), regarding the human hand: the UCL-repair (ulnar collateralligament), the SL-repair (scaphalunate ligament), the collateralligaments repair, the flexor tendon reattachment, or the capsularreattachment of the metacarpophalangeal joint, and regarding the humanfoot: the Bromström ligament repair, treatment of the medialcapsulorrhaphy hallus valgus, or the peroneal retinacular repair.

The distal end of the device according to the invention, which is shownin FIGS. 1 to 3 and the fixation method carried out which the aid ofsuch a device may be varied e.g. in the following manner withoutdeparting from the basic idea of the invention:

Instead of the illustrated catch elements 12 and 12′, any per se knownpair of catch elements may be used, wherein it is advantageous to designthe catch elements such that, at least during the fixation process,friction between the tool 1 and the interface piece 3 is kept as low aspossible and/or is occurring only during a last portion of theadvancement of the interface piece 3 in the axial channel 11 of the tool1.

Instead of the lateral recess 14, the tool 1 may comprise a see-throughportion which allows visual inspection of the movement of the proximalend of the interface piece 3 in the axial channel 11 of the tool 1 andthe suture 4 extends to the outside of the tool through a separateopening or through a slot extending from the distal tool face at leastto the stop 13.

The tool comprises no means for visual inspection.

The recess 14 is narrow but extending right to the distal tool face, theinterface piece 3 comprising for visual control of the fixation processa flag extending into the recess and possibly protruding from the recessand being visible from the outside of the tool 1.

The axial position of the stop 13 is selectable by designing the stop asa separate stop element which can be fixed in the recess 14 in varyingaxial positions, or as a selection of separate stop elements of varyingaxial lengths which can be fixed in the recess 14.

Instead of the system 25 of channels and/or grooves which holds thesuture 4 in a distal region of the anchor foot 22, the anchor footcomprises an eyelet protruding from its proximal face or other suitableproximal means for holding the suture 4 in a slideable manner.

The suture 4 is held in the anchor foot 22 in a non-slideable manner,e.g. with the aid of a knot or suture retainer being retained in adistal recess having a larger cross section than a proximally adjoiningchannel in which the suture extends in a proximal direction, or by asuture end or loop being molded into the anchor foot.

The tool 1 does not comprise a step 16 limiting the axial length of thedistal tool portion 17 having a cross section adapted to fit into thehard tissue opening 5 or the step 16 has a further proximal position.This means that the distal tool end can be introduced into the hardtissue opening 5 to a depth which can be chosen by the surgeon, or thedistal tool end can be introduced into the hard tissue opening to reachthe bottom face of this opening when the fixation process is started.During the fixation process, the distal tool end can then be moveddeeper and deeper into the hard tissue opening while the thermoplasticsleeve 23 gets shorter through liquefaction, the anchor foot 22remaining positioned against the bottom face of the hard tissue opening5. Other than above described in connection with FIG. 1, in such a case,during the liquefaction step it is not the tensioned suture which holdsthe thermoplastic sleeve 23 against the vibrating tool and it is not thebone surface 6 which supports the tool, but both these functions aretaken over by the bottom face of the hard tissue opening. This meansthat the bone tissue of this bottom face needs to have a correspondingmechanical strength while the necessary mechanical strength of thesuture needs to be adapted solely to the tissue attaching function ofthis suture.

The anchor foot 22 is adapted, by e.g. having a tapering or sharpeneddistal end, for being able to be forced at least into cancellous bonewithout the necessity of providing an opening therein beforehand or ofproviding such opening only through the cortical bone. The forcing ofthe anchor foot 22 into the bone tissue is effected by positioning theanchor foot 22 arranged at the distal tool end as shown in FIG. 1 and byapplying a corresponding force to the tool 1, the force beingtransmitted to the anchor foot 22 via the thermoplastic sleeve 23. Theliquefaction process is started by activation of the energy source (e.g.vibration source), only when the anchor foot 22 has reached a desireddepth in the bone tissue. If the forcing of the anchor foot 22 into thebone tissue is to be supported with vibrational energy, transmission ofthe pressing force and the vibration from the tool 1 to the anchor foot22 via the thermoplastic sleeve 23 is to be prevented for preventingundesired liquefaction of the thermoplastic sleeve 23 during the forcingstep. This can be effected by transmitting force and vibration to theanchor foot via the interface piece 3 and by making sure that thethermoplastic sleeve 23 sits only loosely between the distal tool faceand the anchor foot, e.g. by introducing into the recess 14, a blockelement which prevents proximal movement of the interface piece and isable to transmit vibration and force from the tool 1 to the interfacepiece. The block element is to be removed for the anchoring step.

The anchor foot 22 is equipped for being forced into the hard tissue (atleast cancellous bone tissue) without providing an opening beforehand,e.g. by comprising a pointed or otherwise sharp distal end and it isforced into the hard tissue e.g. assisted by ultrasonic vibration,wherein for transmitting the necessary pushing force and the vibrationto the anchor foot 22 the interface piece 3 or another suitable pushingtool is used. The thermoplastic sleeve is either fixed to the anchorfoot or not. When the anchor foot has reached the desired depth and, ifapplicable, after removal of the pushing tool and mounting of theinterface piece 3 on the anchor foot 22, and, if applicable aftermounting the thermoplastic sleeve 23, the distal end of the tool 1 ispositioned on the proximal face of the thermoplastic sleeve and thefixation step is carried out as described above in connection withFIG. 1. Instead of forcing the anchor foot into the hard tissue, it ispossible also to screw it into the hard tissue, wherein the interfacepiece 3 or any other suitable tool can be used for transmitting therotation to the screw-shaped anchor foot.

FIG. 4 shows a proximal end portion of an exemplary embodiment of thedevice having a distal end as e.g. described above in connection withFIGS. 1 to 3. This proximal end portion is shown in axial section andcomprises the proximal end of the tool 1 which is coupled to the energysource 50 (preferably ultrasonic vibration generator) arranged in ahousing 51, and the two end sections of the suture 4 (dash dotted line).The proximal end portion of the device further comprises a lever system52 serving as means for fastening and straightening and/or tensioningthe suture 4 and for moving the anchor foot in a proximal directionrelative to the tool 1 with the aid of the suture 4 extending throughthe anchor foot (as shown in FIG. 1). The lever system 52 is arrangedpreferably on the housing 51 of the energy source 50 but may possiblyalso be arranged on the energy source or on a proximal portion of thetool 1. The lever system 52 is designed for being operated by thesurgeon.

In FIG. 4, the proximal device portion and in particular the named leversystem 52 is illustrated in three configurations (a), (b) and (c) intowhich it is brought in succession for one anchoring process.Configuration (a) serves for introducing the end sections of the suture4 into the lever system. In configuration (b) the end sections of thesuture are fastened by being clamped or braked (through bending aroundat least one small radius) in the lever system and in configuration (c)the fastened end portions of the suture 4 are moved away in a radial andproximal direction from the tool 1 and the housing 51 therebystraightening or tensioning the suture and moving the anchor foot (seeFIG. 1) relative to the tool as soon as liquefaction of thethermoplastic sleeve has started.

The exemplary embodiment of the lever system 52 as illustrated in FIG. 4comprises a clamping arm 53 and a tensioning arm 54, the clamping arm 53being arranged on the housing 51 in a pivoting manner, the tensioningarm 54 being connected in an articulating manner to the free end of theclamping arm 53, and the tensioning arm 54 being longer than theclamping arm 53 and advantageously equipped with an end section suitablefor activating the system by hand (not shown). Each one of the arms 53and 54 of the lever system 52 comprises means for fastening the suturebetween the two arms, e.g. a pair of clamping jaws 55 arranged forclamping the suture end sections between each other when the arms 53 and54 are pivoted relative to each other to extend away from theirarticulating connection in substantially the same direction. The armsare further equipped for being locked to each other (e.g. snapconnection) in this fastening position, wherein the connector functionmay be integrated in the clamping jaws 55.

FIG. 4 also shows the groove 15 which has already been discussed inconnection with FIG. 1 and which preferably reaches right up to theproximal tool end and serves for accommodating the suture 4, wherein thegroove 15 and the lever system 52 are aligned to each other. FIG. 4further shows a suture guide 56 arranged between the groove 15 and thelever system 52.

Fastening the end sections of the suture 4 to the lever system,straightening or tensioning of the suture 4 and moving the anchor footwith the aid of the suture are achieved in the following manner: Forthreading the end sections of the suture 4 through the lever system 52,the two arms are brought into a substantially stretched- out position,advantageously stretched out in a distal direction (configuration (a)).The end sections of the suture 4 running along the groove 15 or, if nogroove is provided, just along the tool 1 towards the proximal tool endare threaded through the suture guide 56 and an eyelet 57 reachingthrough one of the arms 53 and 54 to the one (outer) side of the arms,which, in this arm configuration, faces away from the tool 1. The sutureends are then threaded through a further eyelet 58 on this outer side ofthe tensioning arm 54 to extend, guided by the two eyelets 57 and 58,past the clamping jaw 55 of the tensioning arm 54. The end sections ofthe suture 4 are then held at the free end of the tensioning arm 54 toextend straightened-out but hardly tensioned along the described path(arrow T, configuration (a)). The tensioning arm 54 is then pivotedagainst the clamping arm 53 while the end sections of the suture 4 arestill held at the free end of the tensioning arm 54 until the suture 4is clamped between the clamping jaws 55 and the arms 53 and 54 arelocked relative to each other in the clamping position (configuration(b)). In this configuration the device is checked and possibly tuned byshortly activating the energy source. After such checking and possibletuning, the device is ready for the implantation of the suture anchor.

During such implantation, the suture 4 is tensioned by pulling the freeend of the tensioning arm 54 against the housing 51 thereby moving itsother end, to which the suture end sections are fastened, away from thehousing 51 and in a proximal direction, and the energy source 50 isactivated to start liquefaction. During the liquefaction process, thepressure on the tensioning arm 54 (arrow P in configuration (c)) ismaintained and the free end of the tensioning arm 54 moved closer to thehousing 51 or its other end further away from the housing 51 and moreproximally thereby moving the anchor foot in a proximal direction(configuration (c)).

The lever system 52 as shown in FIG. 4 may further comprise means forcontrolling the suture tension and the liquefaction process or theproximal movement of the anchor foot respectively. For guaranteeing aminimal suture tension or a straight suture extension when the suture isinitially threaded and fastened in the lever system, a roller 59 may beattached to the housing 51 in a resilient manner (e.g. via a spring) tobe positioned between the eyelets 56 and 57. If the suture is passedaround the roller 59, the roller takes up slack in the suture by beingdriven away from the eyelets by the spring. On activation of the leversystem for tensioning the suture, the roller 59 is moved into its mostextended position aligned with the two eyelets. The resiliency of thefixation of the roller 59 can be achieved as illustrated with the aid ofa tension spring but also with the aid of a pressure spring or any otherper se known means (e.g. mechanical, pneumatic or hydraulic) for notonly taking up suture slack and keeping suture tension approximatelyconstant but also for absorbing vibration or shock which may damage thesuture.

The lever system 52 can also take over the function of the stop asdiscussed in connection with FIGS. 1 and 3, in the simplest case byabutting the housing, when the anchor foot has reached its desired mostproximal position. The liquefaction process and its desired end can alsobe controlled via the suture tension by designing a distal portion ofthe tensioning arm to be resilient and therefore to be capable oftensioning the suture with a desired maximum force only and onapplication of more force to just bend. This measure for controlling theliquefaction process not only allows the process to be stopped when thethermoplastic sleeve is exhausted but also when the capacity of the hardtissue to be penetrated by the liquefied material is exhausted and onlya force of an undesired size could press more material into the tissue.This means that in the latter case the liquefaction process iscontrolled independent of the extension of the suture under tension, andin dependence of the hard tissue in which the anchor is to be fixated.Furthermore, limitation of the suture tension e.g. in the named waymakes sure that the suture is not damaged during the fixation process.

FIG. 5 illustrates a further exemplary embodiment of the means forfastening the suture in the lever system and the means for locking theclamping arm 53 and the tensioning arm 54 in the clamping position.Similar items are designated with same reference numerals as in FIG. 4.Instead of the clamping jaws 55 as shown in FIG. 4, the two armscomprise cooperating curved profiles 55.1 which loosely mesh when thetwo arms 53 and 54 are in the clamping position, wherein the curves ofthe curved profiles have a number large enough and/or a radius smallenough for sufficiently braking a suture running between the twoprofiles for preventing suture movement through the gap between theprofiles. The advantage of the fastening means according to FIG. 5 isthe fact that the suture does not need to be clamped and therewith to bedeformed regarding cross section, which may damage a sensitive type ofsuture.

The means for locking the clamping arm 53 and the tensioning arm 54 inthe clamping position as shown in FIG. 5 is a snap connection 55.2comprising a protrusion on the tensioning arm 54 and a correspondingdepression on the clamping arm 53, wherein the protrusion is resilientenough for being snapped into the depression.

Instead of the above described lever system 52, the device may comprisea ratchet mechanism or just a pawl being biased against a surface ofe.g. the housing 51 to clamp the suture end sections against thissurface and being designed for allowing suture movement in only onedirection, or it may comprise any other per se known mechanism whichallows fastening and straightening or tensioning of the suture 4 andmovement of the anchor foot with the aid of the suture while maintainingthe suture tension, wherein the surgeon either operates the mechanism bypulling on the suture ends or the mechanism comprises a member to behandled by the surgeon. In a very simple embodiment of the device theremay be no such means for attaching, tensioning and moving, wherein it isleft to the surgeon to hold on to the suture and tension it and totherewith move the anchor foot.

FIG. 6 illustrates the method as mentioned already further above whichmethod serves for fixation of a suture anchor beyond a hard tissueopening, i.e. in a cavity or soft tissue on a non-accessible side of ahard tissue layer (e.g. in the medullary cavity of a long bone, in alocation underneath a cortical bone layer where there is no cancellousbone tissue, or on the non-accessible side of a bone plate or aprosthesis replacing a bone plate). The device shown in FIG. 6 is asimplified version of the device as shown in FIGS. 1 and 3.

The opening provided for the fixation of the suture anchor 2 is a socalled supra-cortical fixation in which the hard tissue opening providedfor the fixation of the suture anchor does not reach into hard tissue(e.g. into cancellous bone tissue below a cortical bone layer) butreaches through a bone 41 from an accessible side 42 to a non-accessibleside 43 thereof and wherein instead of a subcortical anchorage asupra-cortical button 44 is formed. This supra-cortical button 44 may ormay not be anchored in the bone surface of the non-accessible bone side.The method according to which the fixation is established is quitesimilar to the one as described in connection with FIGS. 1 to 5.

In the simplified embodiment of the device, the suture anchor 2 againcomprises an anchor foot 22 and a thermoplastic sleeve 23, a loop of thesuture 4 being held preferably slideably in the anchor foot (system 25of channels and/or grooves) and end sections of the suture reachingthrough the thermoplastic sleeve 23 and a distal portion 17 of the tool1, which distal tool portion 17 again comprises an axial channel 11 andwhose axial length is determined to be approximately equal to thethickness of the bone 41 by a corresponding position of a step 16. Inparticular, when using a relatively short thermoplastic sleeve 23 it ispossible to not use the interface piece as shown in FIGS. 1 and 3. Byeither fixing the distal face of the thermoplastic sleeve 23 to theanchor foot 22 or by providing energy directors at the distal face 10 ofthe tool 1 or at the proximal face of the thermoplastic sleeve 23,preferable liquefaction of the thermoplastic sleeve at its proximal endis provoked.

If the suture 4 is to still be slideably held by the anchor foot 22 andthe supra-cortical button 44 after the fixation process, it ispreferable to equip the anchor foot 22 with a tube-shaped proximalprotrusion (not shown) reaching into the cannulation of thethermoplastic sleeve 23 and having an axial length at least as great asthe final thickness of the supra-cortical button 44 and/or to use aninterface piece as shown in FIGS. 1 and 3. If slideability of the sutureis not important, the anchor foot 22 can be flat as illustrated, and theinterface piece can be omitted. Therewith the suture may or may not belocked by the liquefied material of the thermoplastic sleeve 23.

Obviously, for the method as shown in FIG. 6, there is no need for thecross section of the thermoplastic sleeve 23 to be adapted to the crosssection of the hard tissue opening 5 such that the sleeve material issituated in close proximity to the wall of the opening as discussed inconnection with FIGS. 1 and 2. It is required that anchor foot 22,thermoplastic sleeve 23 and preferably the distal end of the tool 1 fitinto and trough the opening 5 and that there is enough sleeve materialfor producing a body 44 which cannot pass through the opening 5

Exemplary applications of supra-cortical buttons 44 established as abovedescribed are e.g. regarding the human shoulder: acute acromioclavicularjoint stabilization; and regarding the human foot: fixation ofsyndesmosis disruptions. In the named applications, the suture 4 fixatedby the supra-cortical button may be a suture bundle which is used todirectly replace a tendon or ligament.

FIG. 7 illustrates the per se known double row procedure for suturing asoft tissue to a hard tissue, using the example of reattaching a tornrotator cuff tendon 60 to humeral bone tissue 61 (or a correspondingendoprosthesis) in four successive phases (a), (b), (c) and (d). Phase(a) is before the repair operation and shows the location 62 in whichreattachment is necessary. In phase (b) two medial anchors 63 arefixated in the bone tissue, in locations to eventually be locatedunderneath the tendon 60, each one of the medial anchors 63 attaching atleast one suture 4 to the bone tissue in a slideable manner. In phase(c), the end sections of each suture attached to one of the medialanchors is passed through the torn tendon 60 and by tensioning thesutures away from the tendon end (not shown), the latter is pulled overthe medial anchors 63. In phase (d) two lateral anchors 64 are anchoredin the bone tissue just beyond the edge of the tear, the row of lateralanchors 64 running about parallel to the row of medial anchors 63, theend sections of the sutures 4 being tensioned and locked with the aid ofthe lateral anchors 64 in a cross-wise manner, such that the two sutureend sections held by one medial anchor 63 are locked by two differentlateral anchors 64, such forming crossed suture bridges 65 between therow of medial anchors 63 and the row of lateral anchors 64.

If in a double row procedure in which for establishing the medialanchors 63 methods and devices according to the invention are used it isadvantageous to establish the lateral anchor row using also a fasteningtechnique based on in situ liquefaction of a material havingthermoplastic properties or even similar anchors as described above andbeing further equipped for suture locking (see FIGS. 8 and 9), whereineach row of anchors may comprise two or more than two anchors andwherein each medial anchor 63 is used for attaching at least one suture4 (two suture end portions) and each lateral anchor 64 is used forlocking at least two suture end portions originating from two differentmedial anchors 63.

FIGS. 8 and 9 illustrate a device and method used e.g. for fixatinglateral anchors in the above briefly described double row procedurewherein the suture anchor holding the suture in a slideable manner isfirst fixated in the bone tissue according to the above describedmethod, and then the suture is locked relative to the suture anchor inan additional step, thus eliminating the need for knot-tying. Of coursethe embodiments shown in FIGS. 8 and 9 are also applicable in otherapplications in which such suture locking is required.

FIG. 8 shows the same fixated anchor as FIG. 2, wherein the suture whichafter the fixation process carried out as illustrated in FIG. 1 isslideable relative to the anchor and is then locked in the anchor in alocking step following the fixation step, which two step procedureallows tensioning of the suture after termination of the fixation step.In the locking step, a plug 35 is forced and preferably welded into theproximal mouth of the axial channel 32 of the anchor foot 22, whereinthe suture may be primarily locked by being clamped between plug 35 andanchor foot 22, or primarily by the welding procedure, or by acombination of the two. The plug 35 is positioned and secured as soon asthe suture needs to be finally locked relative to the bone tissue. Forbeing able to be welded to the anchor foot, the plug 35 and the anchorfoot 22 comprise each a thermoplastic material, the two thermoplasticmaterials being weldable to each other preferably using ultrasonicvibration energy which is coupled into the plug 35 by application of asuitable vibration tool (not shown) to the proximal face of the plug 35.It is possible also to fix the plug 35 in the anchor foot 22 by pairinga thermoplastic plug 35 with a rough or otherwise suitably structuredinner surface of channel 32 or a thermoplastic anchor foot 22 with arough or otherwise suitably structured circumferential plug surface andby applying e.g. ultrasonic vibration energy to the plug andsimultaneously forcing the plug into the channel 32. Other per se knownmethods for attaching the plug 35 on the anchor foot 22 and therewithlocking the suture relative to the anchor foot are possible also.

FIG. 9 shows in four successive phases (a) to (d) a further exemplaryembodiment of a suture fixation for which a suture anchor 2 comprisingan anchor foot 22 and a thermoplastic sleeve 23 (e.g. one-piece anchorconsisting of one only material having thermoplastic properties) with aloop of an auxiliary (or substitute) suture 4′ threaded through its foot22 is fixated in a hard tissue opening 5 using the device and method ase.g. described in connection with FIG. 1, wherein the auxiliary sutureloop 4′ takes over the suture function during the fixation according tothe invention and is to be slideable relative to the fixated anchor 2.In phase (a) the anchor 2, the auxiliary suture 4′, the tool 1 and theinterface piece 3 are positioned for the anchoring process in a similarmanner as shown on the left hand side of FIG. 1. In phase (b) the anchor2 is shown after termination of the anchoring process and after removalof the tool 1 and the interface piece 3, in a similar manner as in FIG.2. Phase (b) also shows the suture 4 having a surgical function (e.g.suture pair extending from medial anchors being anchored in a double rowprocedure) and needing locking relative to the bone tissue. Suture 4 isthreaded through the loop of auxiliary suture 4′ and then threadedthrough the anchor foot 22 by the suture loop 4′ being pulled out of theanchor foot. In phase (c) the suture 4 extends through the anchor foot22 and a locking plug 35 to be fixed (e.g. welded, preferably usingultrasonic vibration energy) to the proximal face of the anchor, i.e. tothe remains of the thermoplastic sleeve 23. The locking plug 35advantageously reaches into the axial channel of the thermoplasticsleeve 23 and is fixed in the latter also such securely locking thesuture 4 relative to the anchor 2. Phase (c) also shows a locking tool1′, the locking plug 35 being attached to its distal end e.g. with theaid of a protrusion on the tool and a depression in the proximal face ofthe plug 35. In phase (d) the procedure is terminated, i.e. the suture 4is securely locked relative to the anchor 2 or the bone tissuerespectively. As discussed further above in connection with FIG. 8effective locking of the suture may be effected by mechanical clampingof the suture between the plug 35 and the suture anchor 2, by thewelding together of the two or by a combination of both.

As shown in FIG. 9 it is advantageous (but not necessary) to dimensionanchor 2 and plug 35 such that the plug, when fixed to the anchor, isflush with the bone surface 6. For achieving an additional fixation inthe bone opening it is further advantageous but not necessary todimension the distal end portion 17 of the tool 1 such that it does notfit exactly into the bone opening 5 but such that there is a small gapbetween the wall of this bone opening and the distal tool end 17. Duringthe liquefaction of the material of the thermoplastic sleeve 23,liquefied material will be pressed into this gap and, in the lockingstep, will be welded to the locking plug.

As already described in connection with FIG. 8 the locking plugaccording to FIG. 9 is preferably made of a thermoplastic material whichis weldable to the remains of the thermoplastic sleeve 23 by ultrasonicwelding or comprises a non-liquefiable material and a surface structure(roughness or undercut structure, e.g. thread) which is suitable forforming a positive-fit connection with the remains of the thermoplasticsleeve when forced into the latter under the influence of a pressingforce and ultrasonic vibration. Of course, it is also possible to useother, per se known fixation methods for fixing the locking plug 35 tothe anchor 2 such as e.g. application of an adhesive, thermal welding, asnap connection resulting in a positive-fit connection, or a thread or acombination of a plurality of such fixation methods.

The advantage of using the suture anchor and the fixation and lockingmethod as illustrated in FIGS. 8 and 9 for establishing the lateral rowof anchors in a double row procedure is that the medial and the lateralanchors can be fixated using substantially the same method and the sametools.

FIG. 10 illustrates a further additional step for the method accordingto the invention, the additional step serving for securing the suture 4when tensioned from being damaged by the hard tissue edge around themouth of the bone opening 5 and/or for securing the named edge frombeing damaged by the suture. The fixated anchor 2 shown in FIG. 10 isthe same as the fixated anchor shown in FIG. 2. In the securing step asecuring sleeve 36 is fixated to the remains of the thermoplastic sleeve23 in substantially the same manner as described in connection with FIG.9 for the locking plug 35, wherein the suture 4 extends loosely throughthe securing sleeve 36 and wherein the securing sleeve 36 is againadvantageously dimensioned to be substantially flush with the bonesurface 6 when fixed to the anchor 2 or to slightly protrude from thebone surface 6.

FIG. 11 is an axial section through a suture anchor 2 which comprises ananchor foot 22 and a thermoplastic sleeve 23 and which is suitable forthe device and method according to the invention. The suture anchor 2 asshown in FIG. 11 is preferably a one-piece item and preferably consistsof only one material having thermoplastic properties and being suitablefor the in situ liquefaction constituting one feature of the methodaccording to the invention. The anchor is preferably bio-resorbable.Such a one-piece anchor is mentioned as one exemplary anchor embodimentalready further above (e.g. in connection with FIG. 9) and consists e.g.of PDLLA 70%/30% filled with up to 30% of biphasic calciumphosphate,wherein it may be advantageous to fill the material of the anchor foot22 more than the material of the thermoplastic sleeve 23 or tostrengthen the material of the anchor foot by integrating into it, asmentioned further above, a suture sleeve or a strengthening element e.g.of a polylactide of a higher crystallinity or of hydroxyapatite.

The suture anchor shown in FIG. 11 is e.g. about 15 mm long and has acircular cross section of a diameter of about 3 to 4 mm, the diameter ofthe axial channel of the thermoplastic sleeve 23 amounting to about 2 to3 mm. The system of channels and/or grooves 25 corresponds approximatelyto the one described in connection with FIG. 1 and comprises atransversal channel 30, lateral recesses 31, an axial second channel 32which is coaxial with the axial channel of the thermoplastic sleeve 23and angled third channels 33 connecting the recesses 31 with the secondchannel 32. Therein it is possible to equip the anchor with two (orpossibly more than two) parallel transversal channels 30 foraccommodation of two sutures, the channels either radially or axiallyspaced from each other.

The invention also concerns a vibration tool (sonotrode) which is inparticular suitable for the device and method according to the inventionbut which is applicable in other fields in which vibration energy, inparticular ultrasonic vibration energy is to be used for fixating animplant to hard tissue, in particular in the field of minimally invasivesurgery. The vibration tool is characterized by a rod portion and acoupling portion being attached to the proximal end of the rod portion,wherein the proximal end of the rod portion is fixed in an axial bore ofthe coupling portion, preferably by a press-fit connection.

FIGS. 12 to 15 show exemplary embodiments of proximal ends of vibrationtools 70 showing a proximal end of the rod portion 71 being fixed in anaxial bore of the coupling portion 72. FIG. 12 is a lateral view andFIGS. 13 to 15 are possible axial sections. The coupling portion 72comprises coupling means, preferably a threaded bolt 73 designed tocooperate with a coupling means arranged on a vibration source (notshown). Such cooperating coupling means may also be designed for abayonet coupling or similar coupling capable of transmitting mechanicalvibration from the vibration source to the tool with as little energyloss as possible. The coupling portion further comprises the axial bore74 into which the rod portion reaches and in which the rod portion isfixed, preferably by a press-fit connection or other possible fixationssuch as e.g. a thread or bayonet coupling, if applicable, having a screwrotation opposite the screw direction of a thread for coupling thecoupling portion to the vibration source.

In comparison with a vibration tool made as one piece the vibration toolaccording to FIGS. 12 to 15 has several advantages: it makes rodportions of a very small cross section possible; manufacturing the twotool portions separately and then combining them is simpler thanmanufacturing of the tool as one piece; and rod portion and couplingportion can be made of different materials, the rod portion of amaterial advantageous for the vibration transfer and the couplingportion of a material advantageous for the coupling function. The rodportion is preferably a drawn wire, preferably an aluminum wire whichhas a limited bendability and good vibration characteristics, thecoupling portion is preferably made of stainless steel, e.g. implantsteel 1.4441 (X2CrNiMo 18-15-3), a coupling thread of which is lessprone to get damaged in particular if the tool is to be used not onlyonce and for each use is to be de-coupled from the vibration source.However, either rod portion or coupling portion may also be made oftitanium (preferably grade 5), aluminum or stainless steel.

As illustrated in FIGS. 13 to 15, the axial bore of the coupling portion72 in which the rod portion 71 is fixed, preferably press-fitted, may bea blind bore (FIGS. 13 and 14) or a through bore (FIG. 15) into whichthe rod portion is pushed to any suitable depth.

The vibration tool is preferably adapted to the vibration it is totransfer to an implant such as e.g. a suture anchor and therefore has anaxial length which is approximately the same as a half of the wavelength(possibly multiplied with an integer factor) of the named vibration inthe rod portion material. This half wavelength and therewith theshortest theoretical tool length is for vibration of 20 KHz frequency:126.5 mm (titanium grade 5) and 127.5 mm (aluminum); for vibration of 25KHz frequency: 101.2 (titanium grade 5) and 102 mm (aluminum), thenumbers being applicable for coupling of the tool to the vibrationsource at a location of maximum vibration amplitude. Optimal tool lengthin particular for non-constant tool cross sections are best determinedexperimentally.

The above described method for fixation of a suture in hard tissue (e.g.bone tissue) concerns in particular suture anchors suitable for softtissue attachment to hard tissue. In all the described embodiments ofmethods for fixating such suture anchors in hard tissue the sutures maybe safeguarded against damage by heat dissipating from the materialhaving thermoplastic properties when liquefied, by being soaked withliquid (water or saline solution) preferably before being threadedthrough the suture anchor or a part thereof or before being positionedin the hard tissue opening and necessarily before liquefaction of thematerial having thermoplastic properties.

In most parts of the above description, the suture being fixatedrelative to hard tissue is supposed to take over a surgical functionwhen fixated, but also has a specific function in the fixation method,namely the function of holding the anchor or the thermoplastic sleeverespectively against the tool and moving the anchor foot against thetool when the thermoplastic sleeve gets shorter. If the method accordingto the invention is to be used in applications other than suturefixation or in combination with sutures which are not suitable for thenamed fixation functions (e.g. not easily available as shown in FIG. 9or too weak), it is possible to carry out the method with an auxiliarysuture or suture substitute, which is used instead of or in addition tothe suture taking over the surgical function and which is after thefixation removed or clipped, because it has no function any more. Suchsuture substitute may be any flexible and elongated item such as e.g. awire, a ribbon or a suture of suitable characteristics. In the presentdescription, the term suture is to stand not only for sutures to takeover a surgical function when fixated but also for the above describedauxiliary suture or suture substitute having a function only in themethod of fixating the suture anchor.

In most above described methods for fixating a suture anchor in hardtissue, a material having thermoplastic properties is liquefied topreferably penetrate hard tissue or cavities provided in the hard tissueto constitute when re-solidified a positive-fit connection between theanchor or part thereof and the hard tissue of the wall of the opening.Such positive fit connections can in all described cases be achievedalso in a two-step procedure, wherein the walls of the hard tissueopening are pre-treated according to a method as described in thepublications WO-2010/045751 or WO-2009/141252 (Nexilis), the disclosureof which is enclosed herein in its entirety by reference. Therein amaterial having thermoplastic properties is forced in a liquefied stateinto the hard tissue of the wall of the opening to form together withthis tissue a sort of composite material substantially without coatingthis wall with the material having thermoplastic properties. In a secondstep the anchoring process being part of the method according to theinvention is then carried out as described in the present descriptionand in the cited publications, wherein the liquefied material is notable to penetrate the composite material of the wall of the openingestablished in the pre-treatment step, but instead is welded to thecomposite material of this wall. For such welding it is a condition thatthe material having thermoplastic properties used in the second orfixation step is weldable to the material having thermoplasticproperties used in the first or pre-treatment step. Preferably the twomaterials having thermoplastic properties comprise the samethermoplastic polymer.

If the named pre-treatment step is carried out in a manner to form thecomposite material comprising the hard tissue and the material havingthermoplastic material right to the mouth of the hard tissue opening,this mouth is strengthened and therewith has an enhanced capacity toresist being cut by the suture fixated in the hard tissue opening by theanchor fixated therein, when this suture is tensioned, which means thata similar effect as described in connection with FIG. 10 is achieved.

If the named pre-treatment step is carried out only in an outer regionof the hard tissue (e.g. for strengthening a damaged or very thincortical bone layer), the composite material comprising the hard tissueand the material having thermoplastic material will form a ring at themouth of the hard tissue opening serving as a quasi cortical layerunderneath which the suture anchor is then anchored as shown in FIG. 2.

What is claimed is:
 1. A suture anchor suitable for being fixed in ahard tissue opening with the aid of a material having thermoplasticproperties and energy transmitted to the suture anchor for in situliquefaction of at least part of the material having thermoplasticproperties, wherein the anchor comprises an anchor foot and athermoplastic sleeve, and wherein the anchor foot comprises a system ofchannels and/or grooves with a mouth in a proximal face of the anchorfoot, the system being suitable for threading a suture in form of a looptherethrough, the thermoplastic sleeve being arranged or arrangeablecoaxially to said mouth, wherein the thermoplastic sleeve comprises thematerial having thermoplastic properties and is arranged or arrangableat a proximal face of the anchor foot, wherein the anchor furthercomprises a locking element capable of securing the suture in anon-slideable manner relative to the hard tissue or a securing sleevecapable of securing the suture from being damaged by the hard tissueedge around a mouth of the hard tissue opening wherein the lockingelement or the securing element is equipped to be secured relative tothe anchor foot when the anchor foot is in a fixed state.
 2. The sutureanchor according to claim 1, comprising the locking element wherein thelocking element is fixed or fixable to the anchor foot.
 3. The sutureanchor according to claim 1, comprising the locking element wherein thelocking element is fixed or fixable to remains of the thermoplasticsleeve.
 4. The suture anchor according to claim 2, wherein the lockingelement is a locking plug and is welded or weldable into the channel ofthe system of channels and/or grooves or to the remains of thethermoplastic sleeve with the aid of vibrational energy.
 5. The sutureanchor according to claim 3, wherein the locking element is a lockingplug and is welded or weldable into the channel of the system ofchannels and/or grooves or to the remains of the thermoplastic sleevewith the aid of vibrational energy.
 6. The suture anchor according toclaim 1, comprising the securing sleeve wherein the securing sleeve isfixed or fixable to remains of the thermoplastic sleeve.
 7. The sutureanchor according to claim 1, consisting fully of one material havingthermoplastic properties and being suitable for in situ liquefactionwith the aid of vibratory energy, in particular with ultrasonicvibratory energy.
 8. The suture anchor according to claim 2, consistingfully of one material having thermoplastic properties and being suitablefor in situ liquefaction with the aid of vibratory energy, in particularwith ultrasonic vibratory energy.
 9. The suture anchor according toclaim 3, consisting fully of one material having thermoplasticproperties and being suitable for in situ liquefaction with the aid ofvibratory energy, in particular with ultrasonic vibratory energy. 10.The suture anchor according to claim 4, consisting fully of one materialhaving thermoplastic properties and being suitable for in situliquefaction with the aid of vibratory energy, in particular withultrasonic vibratory energy.
 11. The suture anchor according to claim 5,consisting fully of one material having thermoplastic properties andbeing suitable for in situ liquefaction with the aid of vibratoryenergy, in particular with ultrasonic vibratory energy.
 12. The sutureanchor according to claim 6, consisting fully of one material havingthermoplastic properties and being suitable for in situ liquefactionwith the aid of vibratory energy, in particular with ultrasonicvibratory energy.
 13. The suture anchor according to claim 1,constituting one piece being made of PLDLLA 70%/30% filled with up to30% of biphasic calcium phosphate.
 14. The suture anchor according toclaim 2, constituting one piece being made of PLDLLA 70%/30% filled withup to 30% of biphasic calcium phosphate.
 15. The suture anchor accordingto claim 3, constituting one piece being made of PLDLLA 70%/30% filledwith up to 30% of biphasic calcium phosphate.
 16. The suture anchoraccording to claim 4, constituting one piece being made of PLDLLA70%/30% filled with up to 30% of biphasic calcium phosphate.
 17. Thesuture anchor according to claim 5, constituting one piece being made ofPLDLLA 70%/30% filled with up to 30% of biphasic calcium phosphate. 18.The suture anchor according to claim 6, constituting one piece beingmade of PLDLLA 70%/30% filled with up to 30% of biphasic calciumphosphate.
 19. An arrangement comprising a suture anchor according toclaim 1 and an interface piece, wherein the interface piece is designedto be arranged or arrangable at a proximal face of the anchor foot,wherein the interface piece is capable to extend from the anchor footthrough the thermoplastic sleeve and end portions of a suture extendfrom the anchor foot through the interface piece.
 20. The arrangementaccording to claim 19, wherein the interface piece is capable ofpreventing a contact between a suture threadable to the anchor foot anda at least partially liquefied material of the thermoplastic sleeve.